JP2001245874A - Blood collecting tube for measuring red corpuscle sedimentation speed, blood collecting tube holder, protector for carrying blood collecting tube, and method and device for measuring red corpuscle sedimentation speed - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a blood collecting tube to be used in optically measuring the sedimentation speed of red corpuscles in blood. SOLUTION: The blood collecting tube is a cylindrical transparent container with an ID pasted part 1A to which an ID label for discriminating a subject is pasted and a translucent part 1B for measuring the sedimentation speed of red corpuscles. The ID pasted part 1A is an upper cylindrical part with large diameter corresponding to the standard size of the ID label, and the translucent part 1B is a lower cylindrical part with small diameter corresponding to a subject. As for the blood collecting tube 1 for an adult, the lower cylindrical part 1A is shaped as a standard tube with the capacity corresponding to the permissible quantity of blood to be collected for an adult. As for the blood collecting tube 1 for infant, the lower cylindrical part 1A is shaped as a capillary tube with the capacity corresponding to the permissible quantity of blood to be collected for an infant.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a blood collection tube for measuring erythrocyte sedimentation velocity, a blood collection tube holder, a method for measuring erythrocyte sedimentation velocity, and an apparatus therefor. More specifically, the present invention relates to a method for optically measuring the sedimentation velocity of erythrocytes in blood. The present invention relates to a blood collection tube and a measurement technique used for measurement.

[0002]

2. Description of the Related Art The measurement of erythrocyte sedimentation (erythrocyte sedimentation velocity) is one of the most commonly used methods in daily clinical practice. One hour after standing, the person records the height of the blood cell layer caused by sedimentation of red blood cells (the sedimentation height of red blood cells), and determines the speed of sedimentation of red blood cells. The Wester Glen method is used as standard.

[0003]

However, such a measuring method requires a long time of one hour or more from the start to the end of the measurement, and is not suitable as an inspection method when urgent treatment is required.

A blood collection tube used in the above-mentioned Westergren method is a glass tube having an inner diameter of 2.55 mm and a total length of 300 mm. In order to fill the mixed solution of No. 4, about 2 CC of blood is required, which is not suitable for blood tests of infants with a small allowable blood collection amount.

The present invention has been made in view of such a conventional problem, and a main object of the present invention is to provide a blood collection tube used for optically measuring the sedimentation rate of red blood cells in blood. It is another object of the present invention to provide an erythrocyte sedimentation velocity measurement technique that can measure the sedimentation velocity in a short time, accurately, and even with a small amount of a liquid sample using the blood collection tube.

[0006]

In order to achieve the above object, a blood collection tube for measuring erythrocyte sedimentation velocity of the present invention comprises an ID sticking part on which an ID label for identifying a subject is attached, and an erythrocyte sedimentation velocity. And a transparent container having a light-transmitting portion for measurement.
A large-diameter upper cylindrical portion having a diameter corresponding to the standard size of the label, and the translucent portion is a small-diameter lower cylindrical portion having a diameter corresponding to the subject. I do.

In a preferred embodiment, the upper cylindrical portion has an outer diameter corresponding to a standard size of the ID label. Also, in the blood collection tube used for adult testers,
The lower cylindrical portion is in the form of a standard tube having an inner diameter and a length having an inner volume corresponding to an allowable blood collection amount of an adult subject, while a blood collection tube used for an infant subject is provided. Is formed in the form of an extra-fine capillary tube having an inner diameter and a length in which the lower cylindrical portion has an inner volume corresponding to an allowable blood collection amount of an infant subject. Further, as a constituent material of the blood collection tube, transparent plastic or transparent glass is preferably used.

The blood collection tube holder of the present invention is suitable for holding the blood collection tube, and comprises at least an upper holding portion for holding an upper portion of the blood collection tube and a bottom portion for holding a bottom portion of the blood collection tube. Holding part, and these upper and lower holding parts are characterized by being relatively arranged so as to hold the blood collection tube in an inclined state, preferably, the upper and lower holding parts, An insertion hole for inserting and supporting the blood collection tube is provided, and an insertion guide portion for facilitating insertion of the blood collection tube into the insertion hole is provided on the upper surface side so as to be continuous with the insertion hole.

Further, the blood collection tube carrying protector of the present invention is used as a protective member for carrying the blood collection tube, and comprises a blood collection tube accommodation portion having a contour corresponding to the outer shape of the blood collection tube. It is characterized by having.

The method for measuring erythrocyte sedimentation velocity according to the present invention uses the blood collection tube, wherein the blood collection tube containing blood for measuring the erythrocyte sedimentation speed is held at a predetermined inclination angle. A natural convection that promotes sedimentation of red blood cells is generated in the blood, light is projected onto the blood collection tube, and light transmitted through the blood collection tube is electrically detected. The method is characterized in that the depth dimension of the plasma, which is the supernatant therein, is calculated, and the sedimentation speed of the blood cell layer such as red blood cells, which is the sediment, is measured.

Further, the first erythrocyte sedimentation velocity measuring device of the present invention is for performing the above-mentioned erythrocyte sedimentation velocity measurement method, and inclines the above-mentioned erythrocyte sedimentation velocity measurement blood collection tube containing blood. Tilt holding means for holding in a shape,
A light projecting means for projecting light onto the blood collection tube, and a light receiving means provided opposite to the light projecting means with the blood collection tube interposed, for receiving light transmitted through the blood collection tube from the light projecting means and performing photoelectric conversion Means, a light amount change measuring means for measuring a temporal change in the output of the light receiving means, and a sedimentation speed of a blood cell layer such as red blood cells which is a precipitate in the blood collection tube is calculated based on a measurement result of the light amount change measuring means. Erythrocyte sedimentation velocity calculating means.

A second apparatus for measuring erythrocyte sedimentation velocity according to the present invention is also for performing the above-described method for measuring erythrocyte sedimentation velocity. A plurality of inclined holding means, a plurality of these inclined holding means are arranged on the circumference, and a turntable rotatably supported around its central axis, and the turntable is driven to rotate. A rotation driving unit that stops indexing so that any one of the blood collection tubes is positioned at the measurement position, a light projecting unit that projects light onto the blood collection tube positioned at the measurement position, A light-receiving means for receiving the light transmitted through the blood collection tube from the light-emitting means and photoelectrically converting the light transmitted from the light-emitting means, and measuring a temporal change in the output of the light-receiving means; A blood cell such as a red blood cell which is a sediment in the blood collection tube based on a measurement result of the light quantity change measuring means, a control means for controlling the light quantity change measuring means and the rotation driving means in synchronization with each other, A settling speed calculating means for calculating a settling speed of the layer.

Preferably, the blood collection tube holder is used as the inclined holding means. The blood collection tube holder includes a standard blood tube having a lower cylindrical portion in the form of a standard tube, and a capillary tube. A capillary holder capable of inserting the blood collection tube having the lower cylindrical portion in the form and a structure capable of tilting and holding, whereby a configuration capable of measuring erythrocyte sedimentation velocity with various types of blood collection tubes having different shapes and dimensions. In this case, the blood collection tube holder desirably includes detection means for specifying the two types of blood collection tubes.

In the present invention, by holding the blood collection tube containing the blood collected therein in an inclined shape, a natural convection is generated in the blood to accelerate the sedimentation speed of the red blood cells, and the blood cell layer (the red blood cells and the like are collected and sedimented). Along with the sedimentation in ()), a boundary between the plasma as a supernatant and the blood cell layer as a sediment appears in the blood collection tube. This boundary descends with time in the blood collection tube, and after a certain period of time, the lowering of this boundary stops (sedimentation of the blood cell layer stops).

When light is projected on the blood collection tube,
The amount of light transmitted through the blood in the blood collection tube varies according to the transparency of the blood collection tube (corresponding to the erythrocyte sedimentation state of the blood), and a space above the plasma as a supernatant (a space without blood), a plasma The light transmitted through the blood cell layer as the sediment can be clearly distinguished from each other, and by detecting the change in the amount of transmitted light, the boundary between the plasma liquid surface and the plasma and the blood cell layer can be reliably grasped.

Therefore, by detecting the change in the amount of light transmitted through the blood collection tube using a light receiving element such as a CCD line sensor, a photodiode array, or a CCD area sensor, the detected value changes over time. And the depth of the blood cell layer is calculated from the calculated value and the measurement time.

For example, in the case where erythrocyte sedimentation is measured using a mixture of sodium citrate solution 1 and blood 4 in a volume ratio, the boundary between the sedimented blood cell layer and the supernatant, plasma, and the plasma mixed The amount of light passing through the boundary with the space where there is no liquid, that is, the amount of light passing through the plasma liquid surface, changes greatly.
Alternatively, by detecting using a CCD area sensor or the like, the temporal change in the depth of plasma can be captured in real time, and the maximum depth dimension can also be calculated, thereby enabling erythrocyte measurement. .

The effect of accelerating the sedimentation rate of erythrocytes by holding the blood collection tube in an inclined manner does not change even when the blood collection tube is an ultrafine tube (capillary tube). Can be measured safely, quickly and reliably.

[0019]

Embodiments of the present invention will be described below in detail with reference to the drawings.

Embodiment 1 FIG. 1 shows an apparatus for measuring erythrocyte sedimentation velocity according to the present invention. This apparatus specifically measures the red sedimentation of blood contained in a blood collection tube 1 as shown in FIG. 2, and includes a plurality (eight in this embodiment) of blood collection tubes 1, 1 ,... Are held at an inclined angle, preferably at an angle of 15 ° to 25 °.
Are arranged on a circumference, and the turntable 3 is connected to a rotation shaft 3a of the turntable 3 to rotate the turntable 3 to a measurement position. A pulse motor (pulse motor with speed reducer) 4 which is a rotary driving means for stopping the rotation, a light projecting means 5, a light receiving means 6, a position detecting means 7 for detecting a stop position of the turntable 3, and a light quantity change measuring means. A signal processing unit 8, a control unit 9 as a control unit, and a calculation processing unit 10 as a sedimentation speed calculation unit are configured as main units.

The blood collection tube 1 is for collecting blood for measuring the sedimentation velocity of erythrocytes. Specifically, as shown in FIG. 2, the blood collection tube 1 includes an ID sticking section 1A and a light transmitting section 1B. It is in the form of a thin circular tubular transparent container. This blood collection tube 1
As the constituent material, transparent plastic or transparent glass is preferably used. The blood collection tube 1 of the illustrated embodiment is excellent in mass productivity and is made of a transparent plastic excellent in impact strength from the viewpoint of ensuring safety in handling. It is an integrally molded product.

The ID attaching section 1A includes an ID for identifying a subject.
A portion to which the label 40 is attached, which is in the form of a large-diameter upper cylindrical portion provided above the blood collection tube 1. This ID
Specifically, the shape and size of the attaching portion 1A have an outer diameter corresponding to the standard size of the ID label 40, and the ID label 40 attached to the cylindrical surface of the ID attaching portion 1A can be easily and reliably identified. Structure.

The light transmitting portion 1B is a portion for measuring the sedimentation speed of red blood cells, and the ID attaching portion 1A of the blood collection tube 1 is provided.
Is formed in the form of a small-diameter lower cylindrical portion provided continuously to the lower end of the lower cylindrical portion. Specifically, the shape and dimensions of the light transmitting portion 1B are different from those for the adult examiner shown in FIG.
(B) for infants and other infants,
It has a different configuration.

That is, as shown in FIG. 2A, the translucent portion 1B of the blood collection tube 1 for an adult examiner has an inner diameter corresponding to an inner volume corresponding to an allowable blood collection amount of an adult subject. It is in the form of a standard tube having a length dimension.

On the other hand, as shown in FIG. 2 (b), the translucent portion 1B of the blood collection tube 1 for the infant subject has an inner diameter corresponding to an internal volume corresponding to the allowable blood collection amount of the infant subject. And a very thin capillary tube having a length dimension.

The boundary between the ID sticking portion 1A and the light transmitting portion 1B is tapered downward as shown in FIG.
The two parts 1A and 1B are formed in such a shape that the two parts 1A and 1B continuously draw a gentler cross-sectional curve as much as possible so that excessive stress concentration does not occur at this part.

The blood collection tube holder 2 holds the blood collection tube 1 in which blood is collected and stored in an inclined manner, and a plurality (eight in the illustrated example) is provided on the turntable 3 at equal intervals in the circumferential direction. It is arranged on the circumference.

That is, as shown in FIG. 3, the turntable 3 of the illustrated embodiment is provided with eight ribs 3b, 3b,... Extending radially at the tip of the rotating shaft 3a. The blood collection tube holder 2 is attached and fixed to the distal end portion at a predetermined inclination angle, preferably 15 ° to 25 °, in the circumferential direction.

In FIG. 1, the direction of inclination of the blood collection tube holders 2, 2,... Is drawn in a direction parallel to the paper surface. It is drawn, and is actually inclined at right angles to the paper.

As shown in FIGS. 4 and 5, the blood collection tube holder 2 is in the form of a skeleton tube made of a resin material or the like. The main part includes a portion 2a and a bottom holding portion 2b that holds the bottom of the blood collection tube 1.

The upper and lower holders 2a, 2b
Are relatively arranged so as to hold the blood collection tube 1 in an inclined state. Specifically, the upper and lower holding portions 2a, 2b
Has insertion holes h1 and h2 for inserting and supporting the blood collection tube 1, respectively. As described above, the insertion holes h1 and h2 are arranged relative to each other so that the blood collection tube holder 2 is held at a predetermined inclination angle (the state shown in FIGS. 1, 4 and 5). The axis of h2 is also provided with the same inclination angle corresponding thereto.

The insertion hole h1 of the upper holding part 2a is
The ID attaching portion 1A is held in a cylindrical hole having an inner diameter corresponding to the outer diameter of the ID attaching portion 1A for this purpose. On the other hand, the insertion hole h2 of the lower holding portion 2b is
The distal end portion of the light-transmitting portion 1B of the blood collection tube 1 is held. For this purpose, a cylindrical hole having an inner diameter corresponding to the outer diameter of the light-transmitting portion 1B is formed. It has an arcuate cross-sectional shape as shown. A thin through-hole 25a is formed in the bottom 25, and the through-hole 2a is formed.
5a has both a function as a drain hole for the insertion hole h2 and a function as a mounting hole for a sample sensor (not shown) for detecting the presence or absence of the blood collection tube 1.

Further, insertion holes h1, h of the blood collection tube holder 2
2 is a lower cylindrical portion in the form of a standard tube, that is, a light transmitting portion 1
B (see FIG. 2 (a)) and a blood collection tube 1 having a light-transmitting portion 1B in the form of a capillary tube (see FIG. 2).
(See (b)).

That is, the insertion holes h1 and h2 are designed corresponding to the shape and size of the standard tube. In the case of the standard tube, the insertion holes h1 and h2 are directly inserted and held. In the case of the capillary tube,
It is configured to be inserted and held via a capillary holder 13. The capillary holder 13 is designed so that its inner diameter shape corresponds to the outer shape of the capillary tube, and its outer diameter size shape is designed to correspond to the outer shape of the standard tube.

The two types of blood collection tubes 1 can be detected and distinguished by two microswitches MS1 and MS2 attached as detection means to the lower left side of the blood collection tube holder 2. That is, the micro switches MS1 and MS
When both of the two are ON, the standard tube is used as the blood collection tube 1, and the microswitch MS1 is ON and M
When S2 is OFF, it is determined that the capillary tube is used as the blood collection tube 1.

With such a structure,
Erythrocyte sedimentation velocity measurement is possible with various types of blood collection tubes having different shapes and dimensions.

On the upper surface side of the upper and lower holding portions 2a and 2b, insertion guide portions 30a and 30b are provided with the insertion holes h.
1 and h2, respectively, and the insertion hole h
1 and h2, the structure is such that the blood collection tube 1 can be easily and reliably inserted.

The light projecting means 5 is positioned at the measurement position.
This is for projecting light (projection light) 14a onto the blood collection tube 1 in which blood, which is a sample, is collected and stored.
D, and a light diffusing plate 15 for uniformly and uniformly applying the projection light 14a from the light emitting source LD to the blood collection tube 1. In the present embodiment, the light diffusion plate 15 includes the blood collection tube holders 2, 2,. (See FIGS. 3 and 4 (c)).

As the light emitting source LD, an LED (light emitting diode) array, preferably a red LED array or the like is used, and the light emitting source LD and the light diffusing plates 15, 15,. The tilt angle is set.

The light receiving means 6 receives the light transmitted from the light projecting means 5 through the blood collection tube 1 at the measurement position and performs photoelectric conversion. They are provided facing each other. Specifically, the light receiving means 6
Is a CC arranged opposite to the light projecting means 5 with the blood collection tube 1 interposed therebetween.
A line sensor LS such as a D line sensor or a photodiode array, and an objective lens LL for converging the light 14b from the light emitting source LD transmitted through the blood collection tube 1 to the line sensor LS are provided.

The position detecting means 7 is a means for accurately stopping the turntable 3 at the measurement position of the blood collection tube 1.
The analog amplifier 16 and the A / D conversion circuit 17 are main components, and the photoelectric conversion output V of the line sensor LS is used for detection.

The photoelectric conversion output V of the line sensor LS changes according to the amount of light transmitted corresponding to the blood in the blood collection tube 1 as shown in FIG. That is, the permeation amount of the space S0 where no sample is present is indicated by Va, and then the permeation amount of the sample S1 (plasma) is reduced to Vb due to the attenuation of the light due to the presence of the plasma, and becomes the sample S2 (blood cell layer). ) Is almost equal to zero because of the presence of blood cells.

The position detecting means 7 calculates the photoelectric conversion output Va
Is used. That is, when measuring the erythrocyte in a certain blood collection tube 1, the turntable 3 starts rotating at the same time as the measurement starts, and when the blood collection tube 1 approaches the measurement position, the light from the LED array LD emits the space in the blood collection tube 1. Start transmitting through S0,
The slight photoelectric conversion output Va from the line sensor LS (FIG. 7)
A broken line 20) is detected.

Then, the photoelectric conversion output Va is A / D converted by the A / D conversion circuit 17 and is taken into the arithmetic processing unit 10. As a result, a deceleration command of the pulse motor 4 is given to the control unit 9. Then, the turntable 3 changes from the constant speed rotation mode to the deceleration rotation mode.

When the turntable 3 rotates at a reduced speed, the photoelectric conversion output Va gradually increases and reaches a maximum value (broken line 21 in FIG. 7), and then decreases and becomes 0 when the blood collection tube 1 moves away from the measurement position. The value of the photoelectric conversion output Vamax at this time is stored in the arithmetic processing unit 10.

Subsequently, an instruction to increase the speed of the pulse motor 4 is given to the control unit 9, and the turntable 3 returns from the deceleration rotation mode to the constant speed rotation mode. When the blood collection tube 1 approaches the measurement position again, the above-described operation is performed. As described above, the turntable 3 rotates at a reduced speed, and the photoelectric conversion output Va follows the same temporal change as described above. At this time, the value of the photoelectric conversion output Va and the photoelectric conversion output Vamax stored last time are calculated as follows. The arithmetic processing unit 10 makes a comparison during the deceleration rotation mode, and this Va is Vamax.
When it is equal to or decreases, a stop command of the pulse motor 4 is given to the control unit 9 to stop the turntable 3.

The signal processing section 8 measures a change with time of the output of the light receiving means 6. Specifically, the signal processing unit 8
The photoelectric conversion output V of the line sensor LS is detected, and the change with time is measured. This output change corresponds to the contents of the blood collection tube 1 as described above, for example, as shown in FIG. 7, where Va represents the amount of light received through the space S0 and Vb represents the sample 1 (Plasma) indicates the amount of light received. Sample 2 (blood cell layer) hardly transmits light, and is 0.

The photoelectric conversion output V is calculated at the end of the blood collection tube 1,
In this embodiment, the boundary B1 between the ID label 40 of the blood collection tube 1 and the space S0, the boundary B2 between the space S0 and the plasma S1, and the boundary B3 between the plasma S1 and the blood cell S2 greatly change.

The phase between the boundary B1 and the boundary B2 does not change for the same blood collection tube, but only the boundary B3 changes. That is, although the boundary B3 does not exist at the start of the measurement, a short time after the start of the measurement, when the aggregate of red blood cells settles and starts to accumulate, the boundary B3 is generated with the elapse of time and the boundary B3 is lowered (FIG. 7). Arrow G) and move to 22
A photoelectric conversion output Vb is generated at the position indicated by.

Then, at the time when the sedimentation further proceeds and the optimal timing for the measurement of the erosion is set, the boundary B3 is moved to the position 23 in FIG. The photoelectric conversion output Vb at this time is substantially equal to the photoelectric conversion output Vb at the position where the boundary B3 is 22.

The signal processing section 8 processes the photoelectric conversion outputs Va and Vb at the three boundary positions and sends a position pulse (latch signal) to the arithmetic processing section 10.

That is, the photoelectric conversion output V (Va and V
b) is first-order differentiated to obtain a first-order differentiated waveform f ′, and second-order differentiated to obtain a second-order differentiated waveform f ″. Thereafter, a clipping signal A is obtained from a comparison between the primary differential waveform f 'and the set value L1, and a clipping signal D is obtained from a comparison between the primary differential waveform f' and the set value L2. On the other hand, zero cross signals B and E are obtained from the second derivative waveform f ″. Further, the position pulse (latch signal) C at the boundary B1 is obtained from the comparison coincidence between the clipping signal A and the zero-cross signal B, and the position pulse (latch signal) F at the boundary B2 is obtained from the comparison coincidence between the clipping signal D and the zero-cross signal E. Get.

The arithmetic processing unit (settling speed calculating means) 10
Based on the measurement result of the signal processing unit 8, the height dimension of the plasma S <b> 1 in the blood collection tube 1 is calculated to calculate erythema. Specifically, the arithmetic processing unit 10 performs measurement by the signal processing unit 8. From the position pulse (latch signal) F which is transmitted and transmitted, boundaries B2 and B
3, and the erythema is calculated from the measured height and the set measurement time (preferably 15 to 20 minutes).

The arithmetic processing unit 10 also functions as a command unit to the control unit 9 for controlling the pulse motor 4, the LED array LD, the line sensor LS, and the like.

In the above description, the ESR measurement process for one blood collection tube 1 has been described.
Are also measured in the same process. In this case, the specification of the blood collection tube 1 is attached to the upper portion of the blood collection tube 1,
A strip-shaped ID label 4 for identifying who the sample is
0 is read by the ID reading device 24.
As the ID reader 24, a character reader is used when the ID is a character, and a barcode reader is used when the ID is a barcode.

Thus, in the sedimentation velocity measuring device constructed as described above, the blood collection tubes 1 containing the sample by the turntable 3 are rotated with respect to the light projecting means 5 and the light receiving means 6. While projecting the projection light 14a.

At this time, first, the ID reading device 24 reads the ID label 40 on the blood collection tube, and specifies the blood collection tube.

The transmitted light 14b passing through the blood collection tube 1 is detected by the line sensor LS of the light receiving means 6 as described above.
The amount of light is detected as an electric signal, and the stop positioning of the turntable 3 and the erythema measurement are performed.

The measurement result of the ESR is displayed by a display device or a printer (not shown) in a display method based on the International Standard Law.

It is not necessary to set the eight blood collection tubes 1, they may be set with time, and the measurement in the state of being set in a toothless manner can be easily performed by using the ID label 40. I can do it.

In this embodiment, FIG.
The measurement is performed not only on such a standard tube but also on the blood collection tube 1 as a capillary tube as shown in FIG. 2 (b). The measurement can be performed by using the holder 13, and the measuring method in this case is the same as that of the standard tube described above.

FIG. 8 shows a transport protector 50 used for transporting the blood collection tube 1.

That is, as described above, the blood collection tube 1 has a stepped cylindrical shape having different diameters of the large diameter ID attaching portion 1A and the small diameter light transmitting portion 1B.
Although the shape is such that excessive stress concentration does not occur at the boundary portion between the D affixing portion 1A and the light transmitting portion 1B, it is liable to be damaged during transportation and handling. In particular, when the blood collection tube 1 is for an infant or a child, the light transmitting portion 1B is in the form of an ultrafine capillary tube as shown in FIG. 2 (b). high.

The transport protector 50 is used as a protective member at the time of transport. The transport protector 50 has a contour corresponding to the outer shape of the blood collection tube 1.
0a. In the illustrated embodiment, two types of the blood collection tube accommodating portions 50a are designed to correspond to the shapes and dimensions shown in FIGS. 2A and 2B, respectively. Is directly inserted into and held in the blood collection tube housing 50a of the transport protector 50 having the blood collection tube housing 50a adapted to the external dimensions of the blood collection tube 1.

Embodiment 2 This embodiment relates to a technique for measuring serum color in plasma in addition to the above-described measurement of red sediment, and uses a measuring device shown in FIG.

This measuring device has exactly the same configuration as that of the first embodiment except for the configuration of the light projecting means 5. That is, although one type of LED array is used as the light source of the light projecting means 5 in the first embodiment, two types of LED arrays having different wavelengths are preferably used in the present embodiment, preferably a red LED array LD1 and a blue LED array LD2. Is used.

In the sedimentation velocity measuring device configured as described above, first, the red LED array LD1 is turned on to perform the red sediment measurement. However, since the red sediment measurement process is exactly the same as in the first embodiment, the description is omitted. I do.

Next, a method of measuring serum color performed after the completion of the red sedimentation measurement step will be described in detail.

That is, at the same time as the completion of the red-sink measurement step, the red LED array LD1 illuminated at the time of the red-sink measurement is continuously lit, and the photoelectric conversion output Vb obtained at this time shown in FIG. A / D conversion is performed and the result is taken into the arithmetic processing unit 10.

Next, the red LED array LD1 is turned off, and the blue LED array LD2 is turned on.
The A / D conversion circuit 17 A / D converts the photoelectric conversion output Vb and takes it into the arithmetic processing unit 10. Then, the two captured values are compared in the arithmetic processing unit 10 and the comparison value is calculated.

This serum color has not been measured so far, and its measured value has not been associated with a disease. However, it is considered that the diagnosis of a disease state will be possible in the future by serum color measurement.

The above-described embodiment merely shows a preferred embodiment of the present invention, and the present invention is not limited to this, and various design changes can be made within the scope.

For example, in the above embodiment, even if the blood collection tube 1 is not set in all eight blood collection tube holders 2, 2,. , An indicator light such as an LED for notifying the presence or absence of the blood collection tubes 1, 1,.

In the above embodiment, the light diffusing plate 1
5 is attached to each of the blood collection tube holders 2, 2,..., But may be configured such that one light diffusing plate is provided between the LED array LD and the blood collection tube holder.

Further, in the illustrated embodiment, a line sensor is used as the light receiving means 6, but an area sensor such as a CCD area sensor may be used.

[0076]

As described above in detail, according to the method of measuring sedimentation velocity of the present invention, natural convection is generated in the measurement solution of erythrocyte by holding the blood collection tube at a predetermined inclination angle, and the aggregate of erythrocytes To speed up its sedimentation rate, which allows for rapid erythrocyte sedimentation measurements, which is very useful when urgent medical action is required. Since natural convection is generated not only by the standard tube but also by a very fine capillary tube or the like, the inclination is effective in the measurement of erythema of a baby.

The blood collection tube for erythrocyte sedimentation velocity measurement of the present invention includes an ID sticking part on which an ID label for identifying a subject is affixed, and a translucent part for measuring the sedimentation velocity of red blood cells. The ID sticking portion is a large-diameter upper cylindrical portion having a diameter corresponding to the standard size of the ID label, and the translucent portion corresponds to the subject. Since it is a small-diameter lower cylindrical portion having the above-mentioned diameter, it has an optimum structure for the above-described method of measuring the sedimentation velocity.

Therefore, by using such a blood collection tube, when optically measuring the sedimentation velocity of red blood cells in blood, the sedimentation velocity is measured in a short time, accurately, and even with a small amount of liquid sample. In addition to the above, it is possible to quickly and surely measure erythrocyte sedimentation not only when the subject is an adult but also for infants with a small allowable blood collection amount.

[Brief description of the drawings]

FIG. 1 is a configuration block diagram schematically showing a sedimentation velocity measuring device according to a first embodiment of the present invention.

FIG. 2 shows blood collection tubes used for erythrocyte sedimentation velocity measurement by the sedimentation velocity measurement device, FIG. 2 (a) is for an adult examiner, and FIG. 2 (b) is for an infant such as a baby. It is for the subject.

FIG. 3 is a plan view showing a relative positional relationship between a light projecting unit, a blood collection tube holder, and a light receiving unit in the sedimentation velocity measuring device.

FIG. 4 shows a schematic configuration of a blood collection tube holder in the same sedimentation velocity measuring device. FIG. 4 (a) is a view as viewed from the arrow P in FIG. 3 when a standard tube is used as a blood collection tube, and FIG. FIG. 4 is a view taken along the arrow P in FIG. 3 when a capillary tube is used as a blood collection tube.
(C) is a view on arrow Q in FIG. 4 (a).

FIG. 5 is an enlarged front sectional view showing a main part of the blood collection tube holder.

FIG. 6 is a diagram illustrating an example of a relative positional relationship between a light projecting unit, a blood collection tube, and a light receiving unit in the sedimentation velocity measuring device.

FIG. 7 In the apparatus for measuring sedimentation velocity, the projection light is applied to the space inside the blood collection tube, plasma (supernatant) and blood cell layer (sediment).
FIG. 4 is a diagram illustrating a line light amount (photoelectric conversion output) of transmitted light when transmitting light through the inside, and a signal processing waveform in a signal processing unit thereof.

FIG. 8 is a front sectional view showing the protector for transporting the blood collection tube.

FIG. 9 is a view showing an example of a relative positional relationship among a light projecting unit, a blood collection tube, and a light receiving unit of a sedimentation velocity measuring apparatus which is a second embodiment according to the present invention and enables a serum color measuring step.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Blood collection tube 1A ID sticking part 1B Light transmission part 2 Blood collection tube holder (tilt holding means) 2a Top holding part 2b Bottom holding part 3 Turntable 4 Pulse motor (Rotation driving means) 5 Light emitting means 6 Light receiving means 7 Position detecting means Reference Signs List 8 signal processing unit (light amount change measuring unit) 9 control unit (control unit) 10 arithmetic processing unit (settling speed calculating unit) 11 standard tube 12 capillary tube 13 capillary holder 14a projection light 14b transmitted light 15 diffuser plate 16 analog amplifier 17A / D conversion circuit 24 ID reader 25 Bottom 40 ID label 50 Transport protector 50a Blood collection tube housing h1, h2 Insertion hole LD LED array (light emitting source) LD1 Red LED array LD2 Blue LED array LL Objective lens LS Line sensor S0 Space S1 Plasma S2 Blood cell layer B1 Boundary between ID label and space B2 Plasma liquid level B3 Boundary between plasma and blood cell layer Va Signal representing transmitted light quantity in space S0 Vb Signal representing transmitted light quantity in plasma S1 MS1 microswitch MS2 microswitch

──────────────────────────────────────────────────続 き Continued on the front page (51) Int.Cl. ⁷ Identification symbol FI Theme coat ゛ (Reference) G01N 35/02 A61B 5/14 300E // G01N 1/00 101 300C 300J 300B 300Z G01F 23/28 HF term (Reference) 2F014 FA03 2G045 AA14 BA08 BA09 CA02 CA25 FA11 FA13 FA34 GC10 HA06 HA09 HA12 HA14 HC01 HC02 HC10 JA01 JA07 2G058 AA09 CA04 CA05 CC14 CC17 CC18 CD04 GA03 GB03 GC05 4C038 KK00 KL00

Claims (20)

[Claims] 1. A blood collection tube for collecting blood for measuring erythrocyte sedimentation velocity, which is an ID sticking part on which an ID label for identifying a subject is affixed, and a transparent part for measuring erythrocyte sedimentation velocity. And a light-transmitting portion, wherein the ID sticking portion is a large-diameter upper cylindrical portion having a diameter corresponding to a standard size of the ID label, and the light-transmitting portion. Is a small-diameter lower cylindrical portion having a diameter corresponding to a subject, the blood collection tube for measuring erythrocyte sedimentation velocity. 2. The blood collection tube for erythrocyte sedimentation velocity measurement according to claim 1, wherein the upper cylindrical portion has an outer diameter dimension corresponding to a standard dimension of the ID label. 3. A standard tube having an inner diameter and a length corresponding to an inner volume corresponding to an allowable blood collection amount of an adult subject, wherein the lower cylindrical portion is in the form of a standard tube. 3. The blood collection tube for erythrocyte sedimentation velocity measurement according to 1 or 2. 4. The lower cylindrical portion is in the form of an extra-fine capillary tube having an inner diameter and a length corresponding to an inner volume corresponding to an allowable blood collection amount of an infant subject. The blood collection tube for erythrocyte sedimentation velocity measurement according to claim 1 or 2. 5. The blood collection tube for erythrocyte sedimentation velocity measurement according to claim 1, wherein the constituent material is a transparent plastic. 6. The blood collection tube for erythrocyte sedimentation velocity measurement according to claim 1, wherein the constituent material is transparent glass. 7. A blood collection tube holder for holding a blood collection tube for collecting blood for measuring erythrocyte sedimentation velocity, comprising at least an upper holding portion for holding an upper portion of the blood collection tube and a bottom portion for the blood collection tube. And a bottom holding portion that is disposed relative to the upper and lower holding portions so as to hold the blood collection tube in an inclined state. 8. The upper and lower holding portions each include an insertion hole for inserting and supporting the blood collection tube,
The blood collection tube holder according to claim 7, wherein an insertion guide portion for facilitating insertion of the blood collection tube into the insertion hole is provided continuously with the insertion hole. 9. A protector for transporting a blood collection tube for collecting blood for measuring erythrocyte sedimentation velocity, comprising a blood collection tube accommodation portion having a contour shape corresponding to the outer shape of the blood collection tube. Blood collection tube transport protector 10. The blood collection tube for erythrocyte sedimentation velocity measurement according to any one of claims 1 to 6, wherein blood for erythrocyte sedimentation velocity measurement is collected and housed at a predetermined inclination angle, and Causing natural convection to promote sedimentation of red blood cells, projecting light onto the blood collection tube, electrically detecting the light transmitted through the blood collection tube, and determining the supernatant in the blood from the change over time of the detected value. An erythrocyte sedimentation velocity measuring method, comprising calculating a depth dimension of plasma as a liquid, and measuring a sedimentation velocity of a blood cell layer such as erythrocytes as sediment. 11. The blood is separated into the plasma and a blood cell layer by the natural convection, and the amount of the transmitted light at a liquid level of the plasma and at a boundary between the liquid level of the plasma and the blood cell layer. The method for measuring the sedimentation velocity of erythrocytes according to claim 10, wherein a depth dimension of the blood cell layer is calculated by detecting a change, and the sedimentation velocity is measured. 12. The method according to claim 1, wherein the blood is collected and stored.
A slope holding unit that holds the blood collection tube for erythrocyte sedimentation velocity measurement in an inclined manner, a light projecting unit that projects light to the blood collection tube, and the light projection unit that sandwiches the blood collection tube. Provided opposite to each other,
A light receiving unit that receives light transmitted through the blood collection tube from the light projecting unit and performs photoelectric conversion, a light amount change measuring unit that measures a temporal change in an output of the light receiving unit, and based on a measurement result of the light amount change measuring unit. And an erythrocyte sedimentation velocity calculating means for calculating the sedimentation velocity of a blood cell layer such as erythrocytes as sediment in the blood collection tube. 13. The method according to claim 1, wherein the blood is collected and stored.
A plurality of inclined holding means for holding the blood collection tube for erythrocyte sedimentation velocity measurement according to any one of the above items 1 to 6 in an inclined manner; A turntable rotatably supported about an axis; a rotary drive means for rotating the turntable and stopping indexing so that one of the blood collection tubes is positioned at a measurement position; and the measurement position. A light projecting means for projecting light onto the blood collection tube positioned at, and provided to face the light projecting means with the blood collection tube interposed therebetween;
A light receiving means for receiving light transmitted through the blood collection tube from the light emitting means and performing photoelectric conversion; a light quantity change measuring means for measuring a temporal change in an output of the light receiving means; a light quantity change measuring means and the rotation driving means And a sedimentation speed calculating means for calculating a sedimentation speed of a blood cell layer such as red blood cells as sediment in the blood collection tube based on a measurement result of the light quantity change measuring means. A sedimentation velocity measuring device, characterized in that: 14. The method according to claim 1, wherein the control unit is configured to detect the presence of blood in the blood collection tube when measuring the erythrocyte sedimentation speed after positioning the turntable to stop rotating while the rotation driving unit is operating at a predetermined rotation speed. The light transmitted through the space that is not received is received by the light receiving means and subjected to photoelectric conversion, the output of the light receiving means is taken into the control means, and when the value taken in is greater than a certain value, the rotation driving means is decelerated, When the captured value is equal to or decreased from the previous captured value, the rotation driving unit is stopped as an optimal value, and in this state, light transmitted through the blood collection tube at the measurement position is electrically detected. 14. The erythrocyte sedimentation velocity measuring apparatus according to claim 13, wherein a depth dimension of the blood cell layer in the blood is calculated from a temporal change of the detected value, and the sedimentation velocity is measured. 15. The blood collection tube holder according to claim 7 or 8, wherein the inclined holding means is a blood collection tube holder having a lower cylindrical portion in the form of a standard tube, and a capillary tube. And a capillary holder having a lower cylindrical portion in the form of a capillary holder capable of inserting the blood collection tube and having a structure capable of tilting and measuring the sedimentation velocity of erythrocytes in various types of blood collection tubes having different shapes and dimensions. The erythrocyte sedimentation velocity measuring device according to any one of claims 12 to 14, characterized in that: 16. The erythrocyte sedimentation velocity measuring device according to claim 15, wherein a detection means for specifying the two kinds of blood collection tubes is provided in the inclination holding means. 17. The light-emitting device according to claim 12, wherein a light-scattering plate for scattering light is provided between the light-projecting means and the tilt holding means. Erythrocyte sedimentation velocity measuring device. 18. The erythrocyte sedimentation velocity measuring apparatus according to claim 12, wherein said light projecting means comprises a line light source, and said light receiving means comprises a line sensor. 19. The apparatus for measuring erythrocyte sedimentation velocity according to claim 12, wherein said light projecting means comprises a line light source, and said light receiving means comprises an area sensor. 20. The erythrocyte sedimentation velocity measurement according to any one of claims 12 to 19, wherein an inclination angle of holding the blood collection tube by the inclination holding means is set to 15 ° to 25 °. apparatus.